EP1747793B1 - Methods of making catheter shaft tubes - Google Patents
Methods of making catheter shaft tubes Download PDFInfo
- Publication number
- EP1747793B1 EP1747793B1 EP06253924A EP06253924A EP1747793B1 EP 1747793 B1 EP1747793 B1 EP 1747793B1 EP 06253924 A EP06253924 A EP 06253924A EP 06253924 A EP06253924 A EP 06253924A EP 1747793 B1 EP1747793 B1 EP 1747793B1
- Authority
- EP
- European Patent Office
- Prior art keywords
- layer
- catheter
- polymer layer
- polymer
- core wire
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
- 238000000034 method Methods 0.000 title claims description 33
- 229920000642 polymer Polymers 0.000 claims description 56
- 239000000463 material Substances 0.000 claims description 29
- 230000002787 reinforcement Effects 0.000 claims description 22
- 238000002844 melting Methods 0.000 claims description 10
- 230000008018 melting Effects 0.000 claims description 10
- 239000002861 polymer material Substances 0.000 claims description 8
- 229920001903 high density polyethylene Polymers 0.000 claims description 7
- 239000004700 high-density polyethylene Substances 0.000 claims description 7
- 229910052751 metal Inorganic materials 0.000 claims description 7
- 239000002184 metal Substances 0.000 claims description 7
- 238000004519 manufacturing process Methods 0.000 claims description 6
- 229910001220 stainless steel Inorganic materials 0.000 claims description 6
- 230000003014 reinforcing effect Effects 0.000 claims description 5
- 239000010935 stainless steel Substances 0.000 claims description 5
- 238000000576 coating method Methods 0.000 claims description 4
- 229920001778 nylon Polymers 0.000 claims description 4
- 229920000271 Kevlar® Polymers 0.000 claims description 3
- 239000004952 Polyamide Substances 0.000 claims description 3
- 229920002614 Polyether block amide Polymers 0.000 claims description 3
- 239000011248 coating agent Substances 0.000 claims description 3
- 239000011810 insulating material Substances 0.000 claims description 3
- 239000004761 kevlar Substances 0.000 claims description 3
- 229910001000 nickel titanium Inorganic materials 0.000 claims description 3
- HLXZNVUGXRDIFK-UHFFFAOYSA-N nickel titanium Chemical compound [Ti].[Ti].[Ti].[Ti].[Ti].[Ti].[Ti].[Ti].[Ti].[Ti].[Ti].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni].[Ni] HLXZNVUGXRDIFK-UHFFFAOYSA-N 0.000 claims description 3
- 229920002647 polyamide Polymers 0.000 claims description 3
- -1 polyethylenes Polymers 0.000 claims description 3
- 229920000785 ultra high molecular weight polyethylene Polymers 0.000 claims description 3
- 239000004677 Nylon Substances 0.000 claims description 2
- 239000004642 Polyimide Substances 0.000 claims description 2
- 150000002739 metals Chemical class 0.000 claims description 2
- 229920001721 polyimide Polymers 0.000 claims description 2
- 239000004698 Polyethylene Substances 0.000 claims 1
- 239000003365 glass fiber Substances 0.000 claims 1
- 229920000573 polyethylene Polymers 0.000 claims 1
- 229920002635 polyurethane Polymers 0.000 claims 1
- 239000004814 polyurethane Substances 0.000 claims 1
- 239000010410 layer Substances 0.000 description 84
- 229920001343 polytetrafluoroethylene Polymers 0.000 description 8
- 239000004810 polytetrafluoroethylene Substances 0.000 description 8
- 238000002399 angioplasty Methods 0.000 description 7
- 230000008569 process Effects 0.000 description 7
- 230000007704 transition Effects 0.000 description 5
- 238000011282 treatment Methods 0.000 description 5
- 230000008859 change Effects 0.000 description 4
- 238000010276 construction Methods 0.000 description 4
- 238000000151 deposition Methods 0.000 description 4
- 238000001125 extrusion Methods 0.000 description 4
- 238000002583 angiography Methods 0.000 description 3
- 238000005452 bending Methods 0.000 description 3
- 210000004204 blood vessel Anatomy 0.000 description 3
- 239000002131 composite material Substances 0.000 description 3
- 238000013461 design Methods 0.000 description 3
- 239000002904 solvent Substances 0.000 description 3
- 238000005507 spraying Methods 0.000 description 3
- 208000031481 Pathologic Constriction Diseases 0.000 description 2
- 208000007536 Thrombosis Diseases 0.000 description 2
- 230000017531 blood circulation Effects 0.000 description 2
- 230000000295 complement effect Effects 0.000 description 2
- 230000007423 decrease Effects 0.000 description 2
- 238000003618 dip coating Methods 0.000 description 2
- 239000000835 fiber Substances 0.000 description 2
- 230000003902 lesion Effects 0.000 description 2
- 230000000926 neurological effect Effects 0.000 description 2
- 230000002093 peripheral effect Effects 0.000 description 2
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 description 2
- 239000007787 solid Substances 0.000 description 2
- 239000000243 solution Substances 0.000 description 2
- 208000037804 stenosis Diseases 0.000 description 2
- 230000036262 stenosis Effects 0.000 description 2
- 229920002994 synthetic fiber Polymers 0.000 description 2
- 239000012209 synthetic fiber Substances 0.000 description 2
- 230000001225 therapeutic effect Effects 0.000 description 2
- 230000002792 vascular Effects 0.000 description 2
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 description 1
- 229920000049 Carbon (fiber) Polymers 0.000 description 1
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 0.000 description 1
- 229920001651 Cyanoacrylate Polymers 0.000 description 1
- VGGSQFUCUMXWEO-UHFFFAOYSA-N Ethene Chemical compound C=C VGGSQFUCUMXWEO-UHFFFAOYSA-N 0.000 description 1
- 239000004977 Liquid-crystal polymers (LCPs) Substances 0.000 description 1
- MWCLLHOVUTZFKS-UHFFFAOYSA-N Methyl cyanoacrylate Chemical compound COC(=O)C(=C)C#N MWCLLHOVUTZFKS-UHFFFAOYSA-N 0.000 description 1
- 229910000566 Platinum-iridium alloy Inorganic materials 0.000 description 1
- 239000004721 Polyphenylene oxide Substances 0.000 description 1
- 208000012287 Prolapse Diseases 0.000 description 1
- BQCADISMDOOEFD-UHFFFAOYSA-N Silver Chemical compound [Ag] BQCADISMDOOEFD-UHFFFAOYSA-N 0.000 description 1
- 239000004809 Teflon Substances 0.000 description 1
- 229920006362 Teflon® Polymers 0.000 description 1
- 239000004699 Ultra-high molecular weight polyethylene Substances 0.000 description 1
- 206010047163 Vasospasm Diseases 0.000 description 1
- 239000000853 adhesive Substances 0.000 description 1
- 230000001070 adhesive effect Effects 0.000 description 1
- 150000001408 amides Chemical class 0.000 description 1
- 229920006231 aramid fiber Polymers 0.000 description 1
- 229910052788 barium Inorganic materials 0.000 description 1
- DSAJWYNOEDNPEQ-UHFFFAOYSA-N barium atom Chemical compound [Ba] DSAJWYNOEDNPEQ-UHFFFAOYSA-N 0.000 description 1
- 230000015572 biosynthetic process Effects 0.000 description 1
- 238000000071 blow moulding Methods 0.000 description 1
- 229910052799 carbon Inorganic materials 0.000 description 1
- 239000004917 carbon fiber Substances 0.000 description 1
- 239000000919 ceramic Substances 0.000 description 1
- 238000004891 communication Methods 0.000 description 1
- 229910052802 copper Inorganic materials 0.000 description 1
- 239000010949 copper Substances 0.000 description 1
- 238000007887 coronary angioplasty Methods 0.000 description 1
- 238000002788 crimping Methods 0.000 description 1
- 230000003247 decreasing effect Effects 0.000 description 1
- 230000008021 deposition Effects 0.000 description 1
- 230000010339 dilation Effects 0.000 description 1
- 238000007598 dipping method Methods 0.000 description 1
- 230000002526 effect on cardiovascular system Effects 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 230000002708 enhancing effect Effects 0.000 description 1
- 230000001747 exhibiting effect Effects 0.000 description 1
- 239000003000 extruded plastic Substances 0.000 description 1
- 239000011152 fibreglass Substances 0.000 description 1
- 229920002313 fluoropolymer Polymers 0.000 description 1
- 239000004811 fluoropolymer Substances 0.000 description 1
- 239000011888 foil Substances 0.000 description 1
- 238000005755 formation reaction Methods 0.000 description 1
- 239000002783 friction material Substances 0.000 description 1
- 239000003292 glue Substances 0.000 description 1
- 230000036541 health Effects 0.000 description 1
- 238000010438 heat treatment Methods 0.000 description 1
- 238000001802 infusion Methods 0.000 description 1
- 238000002347 injection Methods 0.000 description 1
- 239000007924 injection Substances 0.000 description 1
- 239000007788 liquid Substances 0.000 description 1
- 229920001684 low density polyethylene Polymers 0.000 description 1
- 239000004702 low-density polyethylene Substances 0.000 description 1
- 239000000314 lubricant Substances 0.000 description 1
- 239000003550 marker Substances 0.000 description 1
- 239000007769 metal material Substances 0.000 description 1
- VNWKTOKETHGBQD-UHFFFAOYSA-N methane Chemical compound C VNWKTOKETHGBQD-UHFFFAOYSA-N 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 239000012466 permeate Substances 0.000 description 1
- 229910052697 platinum Inorganic materials 0.000 description 1
- HWLDNSXPUQTBOD-UHFFFAOYSA-N platinum-iridium alloy Chemical class [Ir].[Pt] HWLDNSXPUQTBOD-UHFFFAOYSA-N 0.000 description 1
- 229920000728 polyester Polymers 0.000 description 1
- 239000013047 polymeric layer Substances 0.000 description 1
- 229920000098 polyolefin Polymers 0.000 description 1
- 238000003825 pressing Methods 0.000 description 1
- 229910052709 silver Inorganic materials 0.000 description 1
- 239000004332 silver Substances 0.000 description 1
- 239000000758 substrate Substances 0.000 description 1
- 238000002560 therapeutic procedure Methods 0.000 description 1
- 229920006259 thermoplastic polyimide Polymers 0.000 description 1
- WFKWXMTUELFFGS-UHFFFAOYSA-N tungsten Chemical compound [W] WFKWXMTUELFFGS-UHFFFAOYSA-N 0.000 description 1
- 239000010937 tungsten Substances 0.000 description 1
- 229910052721 tungsten Inorganic materials 0.000 description 1
- 238000007740 vapor deposition Methods 0.000 description 1
- 208000019553 vascular disease Diseases 0.000 description 1
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0009—Making of catheters or other medical or surgical tubes
- A61M25/0012—Making of catheters or other medical or surgical tubes with embedded structures, e.g. coils, braids, meshes, strands or radiopaque coils
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
- A61F2/958—Inflatable balloons for placing stents or stent-grafts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
- A61L29/08—Materials for coatings
- A61L29/085—Macromolecular materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
- A61L29/12—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material
- A61L29/126—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/0045—Catheters; Hollow probes characterised by structural features multi-layered, e.g. coated
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/005—Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/005—Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids
- A61M25/0053—Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids having a variable stiffness along the longitudinal axis, e.g. by varying the pitch of the coil or braid
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/10—Balloon catheters
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M2025/0063—Catheters; Hollow probes characterised by structural features having means, e.g. stylets, mandrils, rods or wires to reinforce or adjust temporarily the stiffness, column strength or pushability of catheters which are already inserted into the human body
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- Veterinary Medicine (AREA)
- Public Health (AREA)
- Engineering & Computer Science (AREA)
- General Health & Medical Sciences (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Hematology (AREA)
- Anesthesiology (AREA)
- Pulmonology (AREA)
- Biophysics (AREA)
- Epidemiology (AREA)
- Vascular Medicine (AREA)
- Transplantation (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Cardiology (AREA)
- Chemical & Material Sciences (AREA)
- Composite Materials (AREA)
- Materials Engineering (AREA)
- Child & Adolescent Psychology (AREA)
- Media Introduction/Drainage Providing Device (AREA)
- Materials For Medical Uses (AREA)
Description
- The present invention relates to methods of making catheters.
- Many catheters have a relatively long and flexible tubular shaft defining one or more passages or "lumens." The end of the catheter that is advanced to a desired site for treatment is customarily referred to as the "distal" end, while the other end is called the "proximal" end. The proximal end of the shaft is generally coupled to a hub for ease of use by a physician. The hub may define one or more proximal ports for communication with the lumen(s) defined by the catheter shaft, and may have a luer-lock fastener or some other means for connecting the catheter to other medical devices or systems.
- Some catheter shafts are made of one or more tubular shaft members, each of which may include any of (he following features, or any combination thereof: one or more polymer layers, one or more types of reinforcing members (such as for example coils, fibers, mesh or braids), one or more stiffening members or wires, and/or a hypotube.
- In those catheter shaft tubes with more than one polymer layer, and also some kind of reinforcement extending between the polymer layers, it may be desirable to select different materials for inner and outer layer(s). For example, a catheter designer might select a lubricious material for an inner layer and stronger material(s) for an outer layer(s). This type of multi-layer design allows greater performance and optimizing various desired properties.
- Because most catheter shaft tubes are of relatively small diameter, the multiple polymer layers are generally assembled from the inner layer outward. Each polymer layer is usually applied to a core wire or mandrel, whether by extrusion, heat-shrinking or other methods, in an operation conducted at or above the melting temperature of the polymer material of that layer. However, if an outer layer is applied to an existing inner layer, and the outer layer melting temperature is greater than that of the inner layer, then the excessive temperature may cause manufacturing difficulties. For example, the inner layer may melt, run, reform, or change thickness in some areas. Another factor is that catheter shaft tubes are generally built up around a metallic core wire or mandrel, which may act as a heat sink during heating operations.
- As a result, the selection of polymer materials available for all but an innermost layer is limited to polymers having melting temperatures equal to or less than that of the innermost layer.
- It would be desirable to be able to select materials for the polymer layers based on performance characteristics and material properties such as strength, flexibility and lubricity, without being limited to outer layers with successively increasing melting temperatures. In other words, it would be desirable to provide tubular members for use in a catheter shaft, of which at least a portion has the following features: at least one inner and outer polymer layer, with reinforcement between the inner and outer layers, in which an outer layer has a higher melting temperature than an inner layer.
- Such a construction would allow the catheter designer to select additional polymer materials for the outer layer(s) of a catheter tube for advantageous performance properties, rather than being limited to materials having low melting temperatures.
- This disclosure of the present invention will include various possible features and embodiments. However, the present invention scope as set forth in each of the claims and is not limited to the particular arrangements described in this disclosure.
- Catheters are used in a variety of therapeutic applications, including intravascular catheters for procedures such as angioplasty and/or deploying medical devices such as stents. Approximately one million angioplasties are performed worldwide each year to treat vascular disease, including coronary, peripheral and neurological blood vessels partially or totally blocked or narrowed by a lesion, stenosis, thrombosis, and/or vasospasm.
- By way of example, the present invention will be described in relation to vascular treatments, including coronary, peripheral and neurological angiography and angioplasty. However, it should be understood that the present invention relates to any claimed method of making such a catheter and/or shaft and is not limited to vascular catheters, angiography, angioplasty, or stents, or even use in blood vessels.
- Common treatment methods for using an angiography or angioplasty catheter include advancing a guidewire into the body of a patient, by directing the guidewire distal end percutaneously through an incision and along a body passage until it is located within or beyond the desired site. The term "desired site" refers to the location in the patient's body currently selected for treatment by a health care professional. When the guidewire is within the catheter guidewire lumen, the catheter may be advanced or withdrawn along a path defined by the guidewire.
- In the case of a balloon catheter, after the balloon is disposed within the desired site, it can be selectively inflated to press outward on the body passage at relatively high pressure to a relatively constant diameter, in the case of an inelastic or non-compliant balloon material. This outward pressing of a constriction or narrowing at the desired site in a body passage is intended to partially or completely re-open or dilate that body passageway or lumen, increasing its inner diameter or cross-sectional area. In the case of a blood vessel, this procedure is referred to as angioplasty. The objective of this procedure is to increase the inner diameter or cross-sectional area of the vessel passage or lumen through which blood flows, to encourage greater blood flow through the newly expanded vessel. The narrowing of the body passageway lumen is called a lesion or stenosis, and may be formed of hard plaque or viscous thrombus.
- Some catheters are used to deliver and deploy stents or other medical devices, in a manner generally known in the art. Stents, for example, are generally tubular scaffolds for holding a vessel or body passage open.
-
EP-1611914 discloses a balloon catheter shaft design for medical treatment of a patient. The balloon catheter allows for further therapeutic dilation or deployment of medical devices such as stents or grafts. At least a potion of the shaft has an inner tubular body defining at least a portion of a guidewire lumen surrounded by an outer tubular body defining at least a portion of an inflation lumen. The proximal portion of the inner body is reinforced by a hypotube. A distal end of the hypotube provides a graduated flexibility transition with a distal spiral-cut segment, in which the pitch of the spiral-cut pattern decreases to provide increase in flexibility. -
WO-95/18647 -
US-2003/0028173 discloses an intravascular catheter including a reinforcement layer having a plurality of interwoven metal wire members and polymer members. The polymer members are thermally processed to permeate the metal wire members to form a polymeric layer having an orientation which is interwoven with the metal wire members. -
US-2004/0207127 discloses a method of producing laminated inflatable, substantially inextensible expander members having composite properties enhancing their use on intravascular catheters, such as angioplasty catheters. Polymeric compounds of different properties are coextruded to create a multi layer parison. The parison is subsequently drawn and expanded in a blow molding operation to yield an expander member exhibiting enhanced properties. -
EP-0807446 discloses a catheter having an elongated tubular body with a distal end, a proximal end and at least one lumen extending therebetween. The body is made from three layers of extruded plastic which adhere to each other. The body has inner and outer layers made from a polymer, and a middle layer also made from a polymer. The middle layer is more flexible and has a lower melt temperature than the inner and the outer layers. -
US 6,858,204 B1 discloses a guiding catheter for use in coronary angioplasty and other cardiovascular interventions which incorporates a plurality of segment of selected flexural modulus in the shaft of the device. The segments which have a different flexibility than the sections immediately proximal and distal to them, creating zones in the catheter shaft which are either more or less flexible than other zones of the shaft. The flexibility and length of the shaft in a given zone is then matched to its clinical function and role. Also disclosed is a process of manufacturing the catheter using a mandrel on which an inner layer, a support layer and an outer layer are applied by extrusion. - It is desirable to provide a catheter having an optimum combination of various performance characteristics, which may be selected among: flexibility, lubricity, pushability, trackability, crossability, low profile and others. Flexibility may relate to bending stiffness of a medical device (catheter and/or stent, for example) in a particular region or over its entire length, or may relate to the material hardness of the components. Lubricity may refer to reducing friction by using low-friction materials or coatings. Pushability may relate to the column strength of a device or system along a selected path. Trackability may refer to a capability of a device to successfully follow a desired path, for example without prolapse. Crossability may be clarified by understanding that physicians prefer to reach the desired site with the catheter while encountering little or no friction or resistance. Profile may refer to a maximum lateral dimension of the catheter, at any point along its length.
- Catheter tubes fabricated according to embodiments of the present invention provide various advantages, which may include: strength, flexibility and smooth transitions thereof, lubricity including a lubricious guidewire lumen, reinforcement, pushability, optimized flexibility along the length of the catheter shaft, torsional strength, pull strength, low profile, etc.
- The scope of the present invention is defined by the appended claims.
- According to a first embodiment of the present invention a catheter may be fabricated by a method of making a tubular body for a catheter shaft, comprising the steps of:
- a. providing a core wire;
- b. coating the core wire with a thermally insulating material;
- c. applying an inner polymer layer having an inner melting temperature onto the coated core wire;
- d. applying one or more reinforcing members to an outer surface of the inner polymer layer; and
- e. applying an outer polymer layer around an outer surface of the inner polymer layer and reinforcement member; the outer polymer layer having an outer melting temperature that is higher than the inner melting temperature; wherein the inner and outer polymer layers and the reinforcement form a tubular assembly around the coated core wire;
- f. releasing and removing the coated core wire from inside the inner polymer layer, such that the remainder forms a catheter shaft tube.
- Embodiments of the invention will now be described by way of example with reference to the accompanying drawings, in which:
-
Figure 1 is an external perspective view of a catheter; -
Figure 2 is an external perspective view of a balloon catheter; -
Figures 3-6 are longitudinal cross-section views of different catheter tubes, each having reinforcement extending between at least two polymer layers; -
Figures 7-12 are transverse cross-section views of various steps in processes for making catheter tubes according to the principles of the present invention; -
Figures 11A and 11B are partial transverse cross-section views of some different possible arrangements during the step shown inFigure 11 ; -
Figures 13 and 14 are partial side elevation views of a balloon catheter stent delivery system, in deflated and inflated states; and -
Figure 15 is a diagrammatic flow chart of a process for making catheter tubes according to the principles of the present invention. - The following description of the preferred embodiments of the present invention is merely illustrative in nature, and as such it does not limit in any way the present invention, its application, or uses. Numerous modifications may be made by those skilled in the art without departing from the scope of the invention, which is defined by the appended claims.
- Generally, the present examples have to do with catheters. and tubes for use in catheter shafts, the present invention has to do with methods of making such tubes and catheters. Referring to the drawings, some examples of catheters are shown in
Figures 1 and2 . Of course, they are only two possible examples of the various types of catheters with shafts having tubes that may be made according to the principles of the present invention. - The
catheter 10 ofFigure 1 has a relatively long and flexibletubular shaft 12, ahub 14, and aflexible strain relief 16. Theshaft 12 extends from a distal end to a proximal end. where thehub 14 andstrain relief 16 are affixed to theshaft 12. Thecatheter 18 ofFigure 2 has aninflatable balloon 20, a relatively long and flexibletubular shaft 22, astrain relief 24, and ahub 26 defining aninflation port 28 and aguidewire port 30. Theballoon 20 is affixed to theshaft 22 near its distal end, and thehub 26 andstrain relief 24 are affixed to the shaft proximal end. Either or both catheters ofFigures 1 and2 may be used with aguidewire 32. -
Catheter 10 defines a passage or lumen extending inside the tubular member(s) of itsshaft 12, which may be used as an infusion or guidewire lumen, for example.Catheter 18 defines at least two lumens, one of which is an inflation lumen connecting the balloon interior with the inflation port for selectively inflating and deflating the balloon. A second lumen defined bycatheter 18 is a guidewire lumen is adapted to receive an elongated flexible guidewire in a sliding fashion. The guidewire andcatheter 18 may thus be advanced or withdrawn independently, or thecatheter 18 may be guided along a path selected with the guidewire. - Some examples of possible designs for tubular bodies are shown in
Figures 3-6 . all of which have at least two polymer layers and some type(s) of reinforcement extending between the layers. -
Figure 3 shows a catheter shaft tube having an inner andouter polymer layer braid 38. Theinner layer 34 may be a lubricious polymer material, such as high density polyethylene (HDPE) or polytetrafluoroethylene (PTFE). Theouter layer 36 is a strong polymer material, which is may be selected to have various other desirable performance properties. For example, the outer layer polymer may be selected for flexibility and strength, and to bond well with the material(s) selected for other components, such as a hub and/or balloon. Examples of acceptable materials include polyamides such as nylons, or polyether block amide (PEBA). - Similarly, the catheter shaft tube of
Figure 5 also has an inner andouter polymer layer Figures 4 and6 show at least an inner and outer polymer layer, and may include a third intermediate layer as well. - In addition, the specific examples shown in
Figures 3-6 also have internal reinforcement in the form of a braid or coil. The reinforcement is depicted in a diagrammatic manner for clarity, and may be one or more wires coiled around the catheter shaft tube, between the inner and outer layers. If more than one wire is used, they may be arranged in a criss-crossing fashion. The wires may be a metal such as stainless steel or nitinol, or another strong material such as an aramid fiber, for example that sold under the trade name Kevlar, or a synthetic fiber based on ultra high molecular weight polyethylene, for example that sold under the tradename Dyneema. - In the example of
Figure 5 , the reinforcement wire(s) 48 is arranged with a pitch angle that is constant along the length of the catheter shaft tube. InFigures 3, 4 and6 . the wires are arranged with a pitch angle that decreases in the distal direction, in other words, the wraps of the wires are closer together near the distal end of tube than at the proximal end. This decreasing pitch, measured in increasing wires per inch ("pics"), may be arranged progressively along the length of the inner body, in linear or non-linear fashion, or in specific segments. - The specific example shown in
Figure 6 has an inner andouter polymer layer reinforcement 54, and a pair ofradiopaque markers 56. Also, the outer polymer layer has multiple segments of differing flexibility. Specifically,outer layer 52 has a proximal, middle, anddistal segment Figure 6 . - The inner surface of catheter shaft tubes may be of a material selected for high lubricity, for example which will present low frictional resistance to movement of a guidewire inserted within the lumen. Some catheters have used an inner layer defining a guidewire lumen that is made of Teflon (PTFE), and it is possible to likewise use PTFE in a catheter according to the present invention.
- Another possibility is to use a different material for the guidewire lumen. Because many guidewires have a PTFE coating, in some operating conditions, it is possible that the resulting interface between similar materials, PTFE tube on PTFE-coated guidewire. to exhibit a slight "slip stiction" effect. Accordingly, another lubricant material may be used, for example HDPE, as the inner layer of inner body.
- One or more radiopaque markers may be provided, to indicate the position of portion(s) of the catheter to a physician using x-ray video. In the example of
Figure 6 , a pair of marker bands made of a radiopaque material are provided near the distal end of the catheter shaft tube. The radio-opaque markers can be made of any densely packed material that creates a discernable feature on a fluoroscopic image. Examples include platinum, a platinum-iridium alloy, tungsten, barium, etc. The markers may be placed on the outside of the catheter shaft tube, or between the inner and outer layers, as shown inFigure 6 . - The markers may be in various shapes and forms, including solid bands, C-shaped bands, foil ribbons, pad printed material in a viscous liquid carrier, injection molded, or applied using non-solid deposition (such as vapor deposition). Some formations are self-fixing to the inner member, while others must be accompanied by a secondary process to secure their location. Such processes include using glue (cyanoacrylate, UV curable, solvent bonding, etc.), crimping, swaging, roiling, or heat fusing.
- The radio-opaque markers can be placed between the inner liner and braid layer, between the braid layer and outer layer, or on the outside of the outer layer. Their location will determine the sequence in which they are applied in the processes above. In the preferred embodiment they are placed between the braid layer and outer layer.
- A proximal portion of the catheter shaft may also be reinforced with a hypotube component. The hypotube may have a flexibility that changes in specific areas. For example, the distal end of the hypotube may be more flexible than its proximal portion. The hypotube may be made of metal which is selected to be biocompatible, such as for example stainless steel. Other acceptable metals may include nitinol, stainless steel, high durometer polymer, or composite materials such as for example fiber glass, carbon fiber, etc.
- The hypotube may be assembled over the outside of the outer layer with a close clearance, longitudinally aligned to the proximal end of the inner member. If desired, a strain relief can be created near its distal end to moderate the change in flexibility between the hypotube reinforcement and the polymer tube. This flexibility transition can be created using a spiral cut pattern at the distal end of the hypotube.
-
Figure 15 depicts a schematic flow chart of one possible method of making a catheter shaft tube according to the principles of the present inventions. A complementary set of cross-sections are shown inFigures 7-12 , which illustrate various stages of an example process of the present inventions. - As shown in
Figure 7 , a core wire or mandrel serves as a foundation or substrate, around which the catheter shaft tube is built up. After the multi-layer tube is fully formed, the core wire will be removed, leaving the catheter shaft tube. The size of the core wire will determine the size of the catheter shaft tube lumen, when the core wire is eventually removed. Various materials may be used for the core wire, including stainless steel or copper, which may be silver-coated. - As shown in
Figure 8 , the core wire is coated with any suitable thermally insulating material, which may be applied by spraying or dip coating. - As shown in
Figure 9 , an inner polymer layer is applied to the core wire by any of several methods: wire mandrel extrusion, dipping or spraying using solvents and/or heat to create a solution of the polymer material, fuse-down techniques such as those employing shrink tubing, or other deposition techniques. According to some embodiments of the present inventions, the purpose of the inner polymer layer is to provide a lubricious inner surface for the lumen of the resulting tube, rather than to substantially contribute to the catheter shaft performance and structural properties. Accordingly, the inner polymer layer may be very thin, for example 0.0127 mm (0.0005 inch) or less. One possible material for the inner polymer layer is high-density polyethylene (HDPE), but many other suitable material choices are possible. - As shown in
Figure 10 , reinforcement is added, which may be of any desired configuration, such as a braid or coil. The reinforcement is applied to the outside of the inner polymer layer. - In the case of a braid, the braider can he arranged in a horizontal, vertical, or suitable other configuration. The braid or coil wire may be round stainless steel wire of a small diameter, such as for example 0.0762 mm (0.003 inch) or less. Of course, many material strands can be used, such as wire with a flat or other profile, different metal materials, natural fibers, polymers, synthetic fibers (Kevlar, LCP's, carbon, etc.), ceramics, and similar selections. Any number of braid wires can be applied simultaneously with the braider, ranging from 1 wire wound clockwise and 1 wire counterclockwise (referred to as "1 over 1"), up to the mechanical limit of a braider's capacity (such as for example 32 over 32).
- The pitch of the reinforcement, which may be measured by the number of wire crossings per inch, called "pics," may be varied over the length of the catheter shaft tube. Thus, the proximal end of the tube may have a higher pitch (and lower pic count), creating a region of higher pushability and greater bending stiffness. Likewise, the distal end may have a lower pitch (and higher pic count), to creating a region of higher flexibility. In between these regions may be a transition zone where the pitch varies from a proximal pitch to a distal pitch. The pitch in this transition zone can change with a linear ramp, a step function with several regions, in a non-linear fashion such as an exponential curve, or some other slope that will produce the desired properties.
- As shown in
Figure 11 , the outer polymer layer is applied to the existing subassembly. The material of the outer polymer layer may be poly-ether block amide (PEBA), and could also be a polyamide such as for example nylon, a polyimide, a fluoropolymer such for example (e.g. FEP, PTFE, etc.), a polyester, a polyolefin (e.g. HDPE. LDPE. PET, etc.), or similar polymers. The outer polymer layer is often designed to be thicker than the inner polymer layer, and may be in the range of 0.0254 - 0.125 mm (0.001-0.005 inch) thick. - The outer polymer layer can be comprised of two or more longitudinal segments that have different material properties. In one embodiment for example, there are three segments of differing flexibilities or durometers, with the proximal segment having the highest durometer, the distal segment having the lowest durometer and greatest flexibility, and the middle segment having an intermediate durometer. The selection and arrangement of material segments can help optimize catheter performance to complement the arrangement of other components: the inner polymer layer, reinforcement, and any other catheter components such as for example a hypotube or an outer polymer tube.
- The construction method of the outer polymer layer will depend on how many longitudinal segments are selected. If the outer polymer layer will be only one segment the whole tube having the same outer polymer layer, then possible methods include: wire mandrel extrusion (in which the subassembly of coated core wire, inner polymer liner, and reinforcement act as a "wire mandrel"); dip coating or spraying using solvents and/or heat to create a solution of the material; or fuse-down techniques such as for example those employing shrink tubing; or other deposition techniques.
- If the outer polymer layer will have two or more longitudinal segments, then possible methods include: fuse-down techniques such as for example those employing shrink tubing; build-up techniques where more (or different) material is selectively placed in the longitudinal regions to have more pushability and bending stiffness: or other deposition techniques.
- As shown in
Figures 11A and 11B , the catheter shaft tube may be made such that the outer polymer layer fills the spaces between the reinforcement members, or spans them. - As shown in
Figure 12 . the coated core wire is then removed, leaving the desired composite catheter shaft tube.
Claims (9)
- A method of making a catheter (10, 18) for medically treating a patient, the method comprising:coating a core wire with a thermally insulating material;applying an inner polymer layer (34, 40, 50) to the core wire;applying one or more reinforcing members to an outer surface of the inner polymer layer (34, 40, 50);applying an outer polymer layer (36, 42, 52) to the reinforcement layer( 38, 48, 54); andreleasing and removing the coated core wire to form a flexible tubular shaft (12, 22) having proximal and distal ends and defining a lumen extending from a proximal port to a distal port;wherein the inner polymer layer (34, 40, 50) has a lower melting temperature than the outer polymer layer (36, 42, 52).
- The method of Claim 1, wherein the reinforcing members are selected from the group of: braids, coils, hoops, woven members, and longitudinal members.
- The method of Claim 1, wherein the reinforcing members are of materials selected from the group of: stainless steel, nitinol, Kevlar, Dyneema, metals, and glass fibers.
- The method of Claim 1, wherein the polymer layers (34, 40, 50; 36, 42, 52) are selected from the group of: polyamides, nylons, polyimides, polyethylenes, polyurethanes, polyether block amides.
- The method of Claim 1, wherein the inner (34, 40, 50) and outer (36, 42, 52) layers are of different polymer materials, the inner layer being lubricious.
- The method of Claim 1 , wherein the tubular shaft (12, 22) has a braided reinforcement extending between the inner (34, 40, 50) and outer (36, 42, 52) layers, and an amount of braid per longitudinal distance changes from a proximal position to a distal position.
- The method of Claim 1, wherein the outer layer (36, 42, 52) is a nylon.
- The method of Claim 1, wherein the outer layer (36, 42, 52) is a polyether block amide.
- The method of Claim 1, wherein the inner layer (34, 40, 50) is high-density polyethylene.
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US11/191,636 US20060030835A1 (en) | 2004-06-29 | 2005-07-27 | Catheter shaft tubes and methods of making |
Publications (2)
Publication Number | Publication Date |
---|---|
EP1747793A1 EP1747793A1 (en) | 2007-01-31 |
EP1747793B1 true EP1747793B1 (en) | 2010-01-20 |
Family
ID=37177777
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP06253924A Expired - Fee Related EP1747793B1 (en) | 2005-07-27 | 2006-07-27 | Methods of making catheter shaft tubes |
Country Status (5)
Country | Link |
---|---|
US (1) | US20060030835A1 (en) |
EP (1) | EP1747793B1 (en) |
JP (1) | JP5335181B2 (en) |
CA (1) | CA2553505C (en) |
DE (1) | DE602006011828D1 (en) |
Families Citing this family (86)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP3505143B1 (en) * | 2002-03-22 | 2022-12-14 | Cardinal Health Switzerland 515 GmbH | Rapid exchange balloon catheter shaft |
US7333840B2 (en) * | 2005-04-25 | 2008-02-19 | Nokia Corporation | Mobile communication terminal |
US9480589B2 (en) * | 2005-05-13 | 2016-11-01 | Boston Scientific Scimed, Inc. | Endoprosthesis delivery system |
KR101143421B1 (en) | 2005-08-16 | 2012-05-22 | 주식회사 일렉콤테프 | Semiconductive tape |
US9445784B2 (en) * | 2005-09-22 | 2016-09-20 | Boston Scientific Scimed, Inc | Intravascular ultrasound catheter |
US8021352B2 (en) | 2006-08-23 | 2011-09-20 | Codman & Shurtleff, Inc. | Unfused catheter body feature and methods of manufacture |
US9950141B2 (en) | 2006-12-29 | 2018-04-24 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Dual braid reinforcement deflectable device (sheath or catheter) |
US9114229B2 (en) | 2006-12-29 | 2015-08-25 | St. Jude Medical, Af Division, Inc. | Dual braid reinforcement deflectable device |
US8182466B2 (en) * | 2006-12-29 | 2012-05-22 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Dual braided catheter shaft |
JP5080094B2 (en) * | 2007-01-30 | 2012-11-21 | 平河ヒューテック株式会社 | Continuation of catheter tube and method for manufacturing catheter tube |
EP2247243B1 (en) * | 2008-01-28 | 2019-05-15 | Baxter International Inc. | Sealant application with malleable section |
US9750625B2 (en) | 2008-06-11 | 2017-09-05 | C.R. Bard, Inc. | Catheter delivery device |
GB0810749D0 (en) | 2008-06-11 | 2008-07-16 | Angiomed Ag | Catherter delivery device |
US8343136B2 (en) * | 2008-08-26 | 2013-01-01 | Cook Medical Technologies Llc | Introducer sheath with encapsulated reinforcing member |
JP2012501803A (en) | 2008-09-10 | 2012-01-26 | イーブイ3 インコーポレイテッド | Stents and catheters with improved stent deployment |
JP5639481B2 (en) * | 2009-02-09 | 2014-12-10 | テルモ株式会社 | Antibacterial medical device manufacturing method and antibacterial medical device |
US9126022B2 (en) | 2009-08-24 | 2015-09-08 | Cook Medical Technologies Llc | Textile-reinforced high-pressure balloon |
US20110238041A1 (en) * | 2010-03-24 | 2011-09-29 | Chestnut Medical Technologies, Inc. | Variable flexibility catheter |
JP5662074B2 (en) * | 2010-07-30 | 2015-01-28 | テルモ株式会社 | catheter |
WO2012047803A2 (en) * | 2010-10-04 | 2012-04-12 | Reverse Medical Corporation | Distal access aspiration guide catheder |
US8515556B2 (en) | 2010-10-29 | 2013-08-20 | Medtronic, Inc. | Reinforced silicone insulation for implantable medical electrical leads |
US8585858B2 (en) * | 2011-06-06 | 2013-11-19 | Alex M. Kronfeld | Medical catheter with bump tubing proximal segment |
WO2012169593A1 (en) * | 2011-06-08 | 2012-12-13 | 株式会社カネカ | Balloon catheter and method for producing same |
US10130789B2 (en) * | 2011-06-30 | 2018-11-20 | Covidien Lp | Distal access aspiration guide catheter |
JP2014521462A (en) | 2011-08-05 | 2014-08-28 | シルク・ロード・メディカル・インコーポレイテッド | Method and system for treating acute ischemic stroke |
EP2572749B1 (en) | 2011-09-23 | 2022-04-27 | Covidien LP | Distal access balloon guide catheter |
US9144661B2 (en) * | 2011-12-05 | 2015-09-29 | Stryker Corporation | Reinforced elongate medical device and method of manufacture |
US9072624B2 (en) | 2012-02-23 | 2015-07-07 | Covidien Lp | Luminal stenting |
GB2501243B (en) | 2012-03-27 | 2014-06-18 | Cook Medical Technologies Llc | Method of making a medical balloon |
US9192499B2 (en) * | 2013-03-11 | 2015-11-24 | Cook Medical Technologies Llc | Inner catheter for a self-expanding medical device delivery system with a closed coil wire |
JP6037946B2 (en) * | 2013-06-10 | 2016-12-07 | オリンパス株式会社 | Stent placement device |
FR3007293B1 (en) * | 2013-06-24 | 2015-12-04 | Balt Extrusion | PROCESS FOR MANUFACTURING A CATHETER AND CATHETER PRODUCED ACCORDING TO THE METHOD |
US9782186B2 (en) | 2013-08-27 | 2017-10-10 | Covidien Lp | Vascular intervention system |
US8968383B1 (en) | 2013-08-27 | 2015-03-03 | Covidien Lp | Delivery of medical devices |
CN105813680A (en) * | 2013-12-19 | 2016-07-27 | 史密斯医疗 Asd 公司 | Soft tip catheter |
US9265512B2 (en) | 2013-12-23 | 2016-02-23 | Silk Road Medical, Inc. | Transcarotid neurovascular catheter |
US9789283B2 (en) * | 2014-02-03 | 2017-10-17 | Medinol Ltd. | Catheter tip assembled with a spring |
US10076634B2 (en) * | 2014-04-25 | 2018-09-18 | Medtronic Ablation Frontiers Llc | Multi-lumen device with non collapsable minor lumen |
US10426497B2 (en) | 2015-07-24 | 2019-10-01 | Route 92 Medical, Inc. | Anchoring delivery system and methods |
US11065019B1 (en) | 2015-02-04 | 2021-07-20 | Route 92 Medical, Inc. | Aspiration catheter systems and methods of use |
AU2016215229B2 (en) | 2015-02-04 | 2020-05-07 | Route 92 Medical, Inc. | Rapid aspiration thrombectomy system and method |
JP2016163643A (en) * | 2015-03-06 | 2016-09-08 | テルモ株式会社 | Catheter and manufacturing method of the same |
US10376363B2 (en) * | 2015-04-30 | 2019-08-13 | Edwards Lifesciences Cardiaq Llc | Replacement mitral valve, delivery system for replacement mitral valve and methods of use |
US10357631B2 (en) * | 2015-05-29 | 2019-07-23 | Covidien Lp | Catheter with tapering outer diameter |
US10568991B2 (en) * | 2015-08-12 | 2020-02-25 | Covidien Lp | Catheter including leak resistant proximal shaft |
US10080862B2 (en) | 2015-08-14 | 2018-09-25 | Medtronic, Inc. | Tubular bodies for medical delivery devices and related manufacturing methods |
US20170072165A1 (en) | 2015-09-11 | 2017-03-16 | Cathera, Inc. | Catheter shaft and associated devices, systems, and methods |
WO2017044131A1 (en) * | 2015-09-11 | 2017-03-16 | Cathera, Inc. | Polymeric catheter shaft with reinforcement |
CN108472474B (en) | 2015-12-21 | 2021-03-19 | 泰尔茂株式会社 | Balloon catheter and medical elongated body |
EP4252992A3 (en) | 2016-02-24 | 2024-01-10 | Incept, LLC | Enhanced flexibility neurovascular catheter |
USD791311S1 (en) * | 2016-05-04 | 2017-07-04 | Doug Yantz Technology, LLC | Catheter sleeve |
EP3484568B1 (en) | 2016-07-13 | 2022-04-27 | Perfuze Limited | High flexibility, kink resistant catheter shaft |
US10653426B2 (en) | 2017-01-06 | 2020-05-19 | Incept, Llc | Thromboresistant coatings for aneurysm treatment devices |
CN114984407A (en) | 2017-01-10 | 2022-09-02 | 92号医疗公司 | System, catheter and catheter advancement device for performing medical procedures in intracranial vessels |
US10376396B2 (en) | 2017-01-19 | 2019-08-13 | Covidien Lp | Coupling units for medical device delivery systems |
EP3593848B1 (en) * | 2017-03-10 | 2022-04-20 | Asahi Intecc Co., Ltd. | Catheter |
US20200215300A1 (en) * | 2017-06-27 | 2020-07-09 | Nipro Corporation | Catheter, separator, and suction system |
EP3925638A1 (en) | 2017-12-15 | 2021-12-22 | Perfuze Limited | Improved catheters and devices and systems incorporating such catheters |
JPWO2019131158A1 (en) | 2017-12-27 | 2020-12-24 | 株式会社カネカ | Catheter and its manufacturing method |
WO2019149680A1 (en) | 2018-01-31 | 2019-08-08 | Teijin Aramid B.V. | Catheter tubular shaft |
CN111787969A (en) * | 2018-03-05 | 2020-10-16 | 美帝诺有限公司 | Catheter system with reinforced guidewire shaft and method of manufacture |
EP3536371B1 (en) * | 2018-03-06 | 2023-01-25 | Phenox Ltd. | Catheter with catheter hub |
US10786377B2 (en) | 2018-04-12 | 2020-09-29 | Covidien Lp | Medical device delivery |
US11123209B2 (en) | 2018-04-12 | 2021-09-21 | Covidien Lp | Medical device delivery |
US11071637B2 (en) | 2018-04-12 | 2021-07-27 | Covidien Lp | Medical device delivery |
US11413176B2 (en) | 2018-04-12 | 2022-08-16 | Covidien Lp | Medical device delivery |
CA3095844A1 (en) | 2018-05-01 | 2019-11-07 | Incept, Llc | Devices and methods for removing obstructive material from an intravascular site |
US11395665B2 (en) | 2018-05-01 | 2022-07-26 | Incept, Llc | Devices and methods for removing obstructive material, from an intravascular site |
EP3793660A2 (en) | 2018-05-17 | 2021-03-24 | Route 92 Medical, Inc. | Aspiration catheter systems and methods of use |
US10953195B2 (en) | 2018-06-01 | 2021-03-23 | Covidien Lp | Flexible tip catheter |
US11517335B2 (en) | 2018-07-06 | 2022-12-06 | Incept, Llc | Sealed neurovascular extendable catheter |
US11471582B2 (en) | 2018-07-06 | 2022-10-18 | Incept, Llc | Vacuum transfer tool for extendable catheter |
US11766539B2 (en) | 2019-03-29 | 2023-09-26 | Incept, Llc | Enhanced flexibility neurovascular catheter |
US11413174B2 (en) | 2019-06-26 | 2022-08-16 | Covidien Lp | Core assembly for medical device delivery systems |
CN114173854B (en) * | 2019-07-31 | 2024-01-12 | 泰尔茂株式会社 | Catheter tube |
AU2020366348A1 (en) | 2019-10-15 | 2022-05-12 | Imperative Care, Inc. | Systems and methods for multivariate stroke detection |
US11638637B2 (en) | 2019-12-18 | 2023-05-02 | Imperative Care, Inc. | Method of removing embolic material with thrombus engagement tool |
CN113365687A (en) | 2019-12-18 | 2021-09-07 | 因普瑞缇夫护理公司 | Method and system for treating venous thromboembolic disorders |
US20210315598A1 (en) | 2019-12-18 | 2021-10-14 | Imperative Care, Inc. | Methods of placing large bore aspiration catheters |
EP4117762A1 (en) | 2020-03-10 | 2023-01-18 | Imperative Care, Inc. | Enhanced flexibility neurovascular catheter |
US11207497B1 (en) | 2020-08-11 | 2021-12-28 | Imperative Care, Inc. | Catheter with enhanced tensile strength |
US20220072272A1 (en) * | 2020-09-08 | 2022-03-10 | Covidien Lp | Catheter including a bamboo structural support member |
US11826520B2 (en) | 2020-12-08 | 2023-11-28 | DePuy Synthes Products, Inc. | Catheter designs for enhanced column strength |
US11786698B2 (en) * | 2020-12-08 | 2023-10-17 | DePuy Synthes Products, Inc. | Catheter with textured surface |
CA3213397A1 (en) * | 2021-03-12 | 2022-09-15 | Hope Medical | Balloon catheter methods of use |
US11944558B2 (en) | 2021-08-05 | 2024-04-02 | Covidien Lp | Medical device delivery devices, systems, and methods |
Family Cites Families (48)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US663614A (en) * | 1899-09-23 | 1900-12-11 | Carl Riedmueller | Advertising device. |
US4646719A (en) * | 1984-06-11 | 1987-03-03 | Aries Medical Incorporated | Intra-aortic balloon catheter having flexible torque transmitting tube |
JPS61255747A (en) * | 1985-05-07 | 1986-11-13 | Sumitomo Metal Ind Ltd | Production of hollow metallic stock |
DE69002295T2 (en) * | 1989-09-25 | 1993-11-04 | Schneider Usa Inc | MULTILAYER EXTRUSION AS A METHOD FOR PRODUCING BALLOONS FOR VESSEL PLASTICS. |
JPH0747173B2 (en) * | 1990-01-31 | 1995-05-24 | 住友金属工業株式会社 | Hot extrusion tube making method and mandrel |
US5217482A (en) * | 1990-08-28 | 1993-06-08 | Scimed Life Systems, Inc. | Balloon catheter with distal guide wire lumen |
US5254090A (en) * | 1991-01-14 | 1993-10-19 | Kontron Instruments, Inc. | Balloon catheter having a dual layer inner member |
US5254107A (en) * | 1991-03-06 | 1993-10-19 | Cordis Corporation | Catheter having extended braid reinforced transitional tip |
ES2105316T3 (en) * | 1992-08-25 | 1997-10-16 | Bard Connaught | EXPANSION CATHETER WITH REINFORCEMENT WIRE. |
US6659977B2 (en) * | 1993-10-27 | 2003-12-09 | Schneider (Europe) A.G. | Multilayer interventional catheter |
DK0650740T3 (en) * | 1993-10-27 | 1999-12-20 | Schneider Europ Gmbh | intervention catheter |
DE69412638T2 (en) * | 1993-12-10 | 1998-12-24 | Schneider Usa Inc | GUIDE CATHETER |
US6024722A (en) * | 1994-01-06 | 2000-02-15 | Scimed Life Systems, Inc. | Thermoplastic polyimide balloon catheter construction |
US5460608A (en) * | 1994-01-25 | 1995-10-24 | Scimed Life Systems, Inc. | Kink free catheter |
US6858024B1 (en) * | 1994-02-14 | 2005-02-22 | Scimed Life Systems, Inc. | Guide catheter having selected flexural modulus segments |
US5454795A (en) * | 1994-06-27 | 1995-10-03 | Target Therapeutics, Inc. | Kink-free spiral-wound catheter |
JPH10509616A (en) * | 1994-11-23 | 1998-09-22 | マイクロ インターベンショナル システムズ インコーポレーテッド | High torque balloon catheter |
US5549552A (en) * | 1995-03-02 | 1996-08-27 | Scimed Life Systems, Inc. | Balloon dilation catheter with improved pushability, trackability and crossability |
US5891112A (en) * | 1995-04-28 | 1999-04-06 | Target Therapeutics, Inc. | High performance superelastic alloy braid reinforced catheter |
US5843050A (en) * | 1995-11-13 | 1998-12-01 | Micro Therapeutics, Inc. | Microcatheter |
US5906606A (en) * | 1995-12-04 | 1999-05-25 | Target Therapuetics, Inc. | Braided body balloon catheter |
JPH09239037A (en) * | 1996-03-04 | 1997-09-16 | Mitsubishi Cable Ind Ltd | Production of tube for medical treatment |
US5851464A (en) * | 1996-05-13 | 1998-12-22 | Cordis Corporation | Method of making a fuseless soft tip catheter |
US5782811A (en) * | 1996-05-30 | 1998-07-21 | Target Therapeutics, Inc. | Kink-resistant braided catheter with distal side holes |
JPH1016001A (en) * | 1996-06-27 | 1998-01-20 | Asahi Chem Ind Co Ltd | Forming of synthetic resin molding with wall of ununiform thickness and mold used for this forming |
US5971975A (en) * | 1996-10-09 | 1999-10-26 | Target Therapeutics, Inc. | Guide catheter with enhanced guidewire tracking |
US5961510A (en) * | 1997-09-26 | 1999-10-05 | Medtronic, Inc. | Flexible catheter |
US5891114A (en) * | 1997-09-30 | 1999-04-06 | Target Therapeutics, Inc. | Soft-tip high performance braided catheter |
US6048338A (en) * | 1997-10-15 | 2000-04-11 | Scimed Life Systems, Inc. | Catheter with spiral cut transition member |
US5891110A (en) * | 1997-10-15 | 1999-04-06 | Scimed Life Systems, Inc. | Over-the-wire catheter with improved trackability |
US6004310A (en) * | 1998-06-17 | 1999-12-21 | Target Therapeutics, Inc. | Multilumen catheter shaft with reinforcement |
DE69937683D1 (en) * | 1998-07-16 | 2008-01-17 | Mark Cohen | REINFORCED TUBE WITH CHANGING STIFFNESS |
US6464684B1 (en) * | 1998-09-09 | 2002-10-15 | Scimed Life Systems, Inc. | Catheter having regions of differing braid densities and methods of manufacture therefor |
US6135937A (en) * | 1998-10-30 | 2000-10-24 | Ballos, Iii; Pete | Moveable tape head for erecting machine |
US6591472B1 (en) * | 1998-12-08 | 2003-07-15 | Medtronic, Inc. | Multiple segment catheter and method of fabrication |
US6171295B1 (en) * | 1999-01-20 | 2001-01-09 | Scimed Life Systems, Inc. | Intravascular catheter with composite reinforcement |
US6500147B2 (en) * | 1999-02-22 | 2002-12-31 | Medtronic Percusurge, Inc. | Flexible catheter |
US6193686B1 (en) * | 1999-06-30 | 2001-02-27 | Advanced Cardiovascular Systems, Inc. | Catheter with enhanced flexibility |
US6488655B1 (en) * | 1999-06-30 | 2002-12-03 | Advanced Cardiovascular Systems, Inc. | Polymer jacket with adhesive inner layer |
US6702802B1 (en) * | 1999-11-10 | 2004-03-09 | Endovascular Technologies, Inc. | Catheters with improved transition |
JP2001190679A (en) * | 2000-01-12 | 2001-07-17 | Hitachi Cable Ltd | Catheter tube and manufacturing method of the same |
JP2001321445A (en) * | 2000-05-17 | 2001-11-20 | Mitsubishi Cable Ind Ltd | Flexible tube |
US6629952B1 (en) * | 2000-12-29 | 2003-10-07 | Scimed Life Systems, Inc. | High pressure vascular balloon catheter |
US6638245B2 (en) * | 2001-06-26 | 2003-10-28 | Concentric Medical, Inc. | Balloon catheter |
US6635047B2 (en) * | 2001-08-06 | 2003-10-21 | Scimed Life Systems, Inc. | Integrated polymer and braid for intravascular catheters |
US20030199914A1 (en) * | 2002-04-23 | 2003-10-23 | Juan-Carlos Diaz | Coaxial balloon catheter |
JP2004033354A (en) * | 2002-07-01 | 2004-02-05 | Terumo Corp | Catheter and method for manufacturing the same |
US7166100B2 (en) * | 2004-06-29 | 2007-01-23 | Cordis Neurovascular, Inc. | Balloon catheter shaft design |
-
2005
- 2005-07-27 US US11/191,636 patent/US20060030835A1/en not_active Abandoned
-
2006
- 2006-07-26 CA CA2553505A patent/CA2553505C/en not_active Expired - Fee Related
- 2006-07-26 JP JP2006203585A patent/JP5335181B2/en not_active Expired - Fee Related
- 2006-07-27 EP EP06253924A patent/EP1747793B1/en not_active Expired - Fee Related
- 2006-07-27 DE DE602006011828T patent/DE602006011828D1/en active Active
Also Published As
Publication number | Publication date |
---|---|
JP5335181B2 (en) | 2013-11-06 |
US20060030835A1 (en) | 2006-02-09 |
JP2007029736A (en) | 2007-02-08 |
DE602006011828D1 (en) | 2010-03-11 |
EP1747793A1 (en) | 2007-01-31 |
CA2553505A1 (en) | 2007-01-27 |
CA2553505C (en) | 2014-03-25 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
EP1747793B1 (en) | Methods of making catheter shaft tubes | |
JP4948791B2 (en) | Balloon catheter shaft structure | |
EP1551489B1 (en) | Wire braid-reinforced microcatheter | |
EP1096965B1 (en) | Reinforced variable stiffness tubing | |
EP0930910B1 (en) | Guide catheter with enhanced guidewire tracking | |
US5951539A (en) | Optimized high performance multiple coil spiral-wound vascular catheter | |
US8308712B2 (en) | Composite laminated catheter with flexible segment and method of making same | |
EP1062965B1 (en) | Guiding catheter with radiopaque band | |
EP1019130B1 (en) | Peripheral vascular delivery catheter | |
AU693357B2 (en) | High performance braided catheter | |
US7674411B2 (en) | Guide catheter having selected flexural modulus segments | |
US20040087933A1 (en) | Stiff guiding catheter liner material | |
US20030135198A1 (en) | Catheter device having multi-lumen reinforced shaft and method of manufacture for same | |
US7172587B2 (en) | Catheter having selectively varied lamination | |
JPH08206215A (en) | Spiral catheter of high performance | |
EP2157994A2 (en) | Hypotube catheter | |
US20070225680A1 (en) | Guiding catheter with chemically softened distal portion and method of making same | |
EP3347078B1 (en) | Polymeric catheter shaft with reinforcement | |
US20040039369A1 (en) | Reinforced multi-lumen medical shaft | |
JP6921660B2 (en) | Guide wire support catheter | |
US20190269884A1 (en) | Catheter system with reinforced guidewire shaft and method of manufacture |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
PUAI | Public reference made under article 153(3) epc to a published international application that has entered the european phase |
Free format text: ORIGINAL CODE: 0009012 |
|
AK | Designated contracting states |
Kind code of ref document: A1 Designated state(s): AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HU IE IS IT LI LT LU LV MC NL PL PT RO SE SI SK TR |
|
AX | Request for extension of the european patent |
Extension state: AL BA HR MK YU |
|
RIN1 | Information on inventor provided before grant (corrected) |
Inventor name: SLAZAS, ROBERT R. Inventor name: SHERMAN, DARREN R. |
|
17P | Request for examination filed |
Effective date: 20070706 |
|
17Q | First examination report despatched |
Effective date: 20070802 |
|
AKX | Designation fees paid |
Designated state(s): BE DE GB NL |
|
RTI1 | Title (correction) |
Free format text: METHODS OF MAKING CATHETER SHAFT TUBES |
|
GRAP | Despatch of communication of intention to grant a patent |
Free format text: ORIGINAL CODE: EPIDOSNIGR1 |
|
GRAS | Grant fee paid |
Free format text: ORIGINAL CODE: EPIDOSNIGR3 |
|
GRAA | (expected) grant |
Free format text: ORIGINAL CODE: 0009210 |
|
AK | Designated contracting states |
Kind code of ref document: B1 Designated state(s): BE DE GB NL |
|
REG | Reference to a national code |
Ref country code: GB Ref legal event code: FG4D |
|
REF | Corresponds to: |
Ref document number: 602006011828 Country of ref document: DE Date of ref document: 20100311 Kind code of ref document: P |
|
REG | Reference to a national code |
Ref country code: NL Ref legal event code: T3 |
|
REG | Reference to a national code |
Ref country code: GB Ref legal event code: 732E Free format text: REGISTERED BETWEEN 20100610 AND 20100616 |
|
PLBE | No opposition filed within time limit |
Free format text: ORIGINAL CODE: 0009261 |
|
STAA | Information on the status of an ep patent application or granted ep patent |
Free format text: STATUS: NO OPPOSITION FILED WITHIN TIME LIMIT |
|
26N | No opposition filed |
Effective date: 20101021 |
|
REG | Reference to a national code |
Ref country code: NL Ref legal event code: SD Effective date: 20110819 |
|
BECA | Be: change of holder's address |
Owner name: CODMAN & SHURTLEFF, INC.325 PARAMOUNT DRIVE,RAYNHA Effective date: 20110920 |
|
BECH | Be: change of holder |
Owner name: CODMAN & SHURTLEFF, INC. Effective date: 20110920 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: DE Payment date: 20140724 Year of fee payment: 9 Ref country code: NL Payment date: 20140710 Year of fee payment: 9 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: GB Payment date: 20140723 Year of fee payment: 9 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: BE Payment date: 20140714 Year of fee payment: 9 |
|
REG | Reference to a national code |
Ref country code: DE Ref legal event code: R119 Ref document number: 602006011828 Country of ref document: DE |
|
GBPC | Gb: european patent ceased through non-payment of renewal fee |
Effective date: 20150727 |
|
REG | Reference to a national code |
Ref country code: NL Ref legal event code: MM Effective date: 20150801 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: DE Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20160202 Ref country code: GB Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20150727 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: NL Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20150801 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: BE Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20150731 |